Method for detecting vagus capture

ABSTRACT

Some embodiments provide a system for delivering neurostimulation. Some system embodiments comprise a lead configured to be implanted in the body, a stimulation output circuit configured to deliver neurostimulation pulses to the vagus nerve through the lead, an EMG sensing circuit configured to use the lead to sense EMG signals from laryngeal muscle activity, and an evoked muscular response detection circuit configured to use the EMG signals sensed by the EMG sensing circuit to detect evoked laryngeal muscle activity evoked by the neurostimulation pulse.

CLAIM OF PRIORITY

This application is a continuation of U.S. application Ser. No.13/586,432, filed Aug. 15, 2012, which claims the benefit of priorityunder 35 U.S.C. §119(e) of Ordonez et al., U.S. Provisional PatentApplication Ser. No. 61/526,568, entitled “SYSTEMS AND METHODS TO DETECTVAGUS CAPTURE”, filed on Aug. 23, 2011, each of which is hereinincorporated by reference in its entirety.

TECHNICAL FIELD

This application relates generally to medical devices and, moreparticularly, to systems, devices and methods for delivering neuralstimulation.

BACKGROUND

Neural stimulation, such as vagus nerve stimulation, has been proposedas a therapy for a number of conditions. Examples of neural stimulationtherapies include neural stimulation therapies for respiratory problemssuch as sleep disordered breathing, blood pressure control such as totreat hypertension, cardiac rhythm management, myocardial infarction andischemia, heart failure (HF), epilepsy, depression, pain, migraines,eating disorders and obesity, and movement disorders.

SUMMARY

Some embodiments provide a method, comprising deliveringneurostimulation pulses to the vagus nerve through an implanted lead,using the implanted lead to sense EMG signals from laryngeal muscleactivity, and using sensed EMG signals to detect evoked laryngeal muscleactivity evoked by the neurostimulation pulses, as recited in the claim.

Some embodiments provide a system for delivering neurostimulation. Somesystem embodiments comprise a lead configured to be implanted in thebody, a stimulation output circuit configured to deliverneurostimulation pulses to the vagus nerve through the lead, an EMGsensing circuit configured to use the lead to sense EMG signals fromlaryngeal muscle activity, and an evoked muscular response detectioncircuit configured to use the EMG signals sensed by the EMG sensingcircuit to detect evoked laryngeal muscle activity evoked by theneurostimulation pulses.

This Summary is an overview of some of the teachings of the presentapplication and not intended to be an exclusive or exhaustive treatmentof the present subject matter. Further details about the present subjectmatter are found in the detailed description and appended claims. Thescope of the present invention is defined by the appended claims andtheir equivalents.

BRIEF DESCRIPTION OF THE DRAWINGS

Various embodiments are illustrated by way of example in the figures ofthe accompanying drawings. Such embodiments are demonstrative and notintended to be exhaustive or exclusive embodiments of the presentsubject matter.

FIG. 1 illustrates increasing vagal stimulation therapy (VST) intensityfrom the left side to the right side of the figure, and furtherillustrates intensity thresholds that elicit various physiologicalresponses to VST.

FIG. 2 illustrates increasing VST intensity from the left side to theright side of the figure, and further illustrates an intensity thresholdfor a laryngeal vibration response that can be used to determine captureand that can further be used as a lower boundary or to determine thelower boundary.

FIG. 3 generally illustrates a right vagus nerve and a recurrentlaryngeal nerve branching off of the right vagus nerve to innervate thelaryngeal muscles near the trachea.

FIGS. 4A and 4B illustrate the latency of the laryngeal muscle activityto a vagus nerve pulse, comparing an ENG signal (FIG. 4A) to an EMGsignal (FIG. 4B).

FIGS. 5-8 illustrate various embodiments for positioning electrodes tostimulate the vagus nerve and record activity of laryngeal muscles usingan EMG signal.

FIGS. 9-10 illustrate results of an experiment in which the vagus nervewas stimulated, an ENG signal reflecting vagal nerve traffic wasrecorded, and EMG signals of laryngeal muscle activity was recordedusing a needle EMG sensor and a lead EMG sensor.

FIGS. 11A-11B illustrate active and passive recharge phases, such as maybe used in various embodiments.

FIG. 12 illustrates a representation of intermittent neural stimulation(INS).

FIG. 13 illustrates a memory, according to various embodiments, thatincludes instructions operable on by stimulation control circuitry tocontrol an up-titration routine by progressively stepping up throughdefined parameter sets where each set incrementally changes thestimulation dose or intensity of the stimulation therapy, according tovarious embodiments.

FIG. 14 illustrates an embodiment of a therapy titration module.

FIG. 15 illustrates an embodiment for titrating stimulation parameters.

FIG. 16 illustrates an embodiment, by way of example and not limitation,of an implantable medical device with a device housing or can and a leadextending from the can.

FIG. 17 illustrates an embodiment of a routine for finding thresholdvalues for each of the electrode configurations.

FIG. 18 illustrates a system embodiment in which an implanted medicaldevice (IMD) is placed subcutaneously or submuscularly in a patient'schest with lead(s) positioned to stimulate a vagus nerve.

FIG. 19 illustrates an IMD placed subcutaneously or submuscularly in apatient's chest with lead(s) positioned to provide a CRM therapy to aheart, and with lead(s) positioned to stimulate and/or inhibit neuraltraffic at a vagus nerve, according to various embodiments.

FIGS. 20-21 are block diagrams illustrating embodiments of a vagus nervestimulation system.

FIG. 22 is a block diagram illustrating an embodiment of an implantablesystem that includes an IMD and an external system.

FIG. 23 is a block diagram illustrating an embodiment of a circuit fordetecting evoked muscular responses.

FIG. 24 is a block diagram illustrating an embodiment of a system fordetecting evoked muscular responses.

FIG. 25 is a block diagram illustrating an embodiment of a circuit forsensing various laryngeal signals.

FIG. 26 is a block diagram illustrating an embodiment of a circuit forsensing various laryngeal signals in context.

FIG. 27 is a flow chart illustrating an embodiment of a method forautomatic threshold adjustment (also referred to as “Auto-Sense”) forevoked response detection during vagus nerve stimulation.

FIG. 28 is a flow chart illustrating an embodiment of a method foradjusting stimulation intensity for vagus nerve stimulation.

FIG. 29 is a flow chart illustrating an embodiment of a method foradjusting stimulation intensity for vagus nerve stimulation duringimplantation of an implantable medical device.

FIG. 30 is a flow chart illustrating an embodiment of a method foradjusting stimulation intensity for vagus nerve stimulation duringfollow-up visits by the patient using the implantable medical device.

FIG. 31 is a flow chart illustrating an embodiment of a method forautomatic capture verification (also referred to as “Auto-Capture”) forvagus nerve stimulation.

DETAILED DESCRIPTION

The following detailed description of the present subject matter refersto the accompanying drawings which show, by way of illustration,specific aspects and embodiments in which the present subject matter maybe practiced. These embodiments are described in sufficient detail toenable those skilled in the art to practice the present subject matter.Other embodiments may be utilized and structural, logical, andelectrical changes may be made without departing from the scope of thepresent subject matter. References to “an”, “one”, or “various”embodiments in this disclosure are not necessarily to the sameembodiment, and such references contemplate more than one embodiment.The following detailed description is, therefore, not to be taken in alimiting sense, and the scope is defined only by the appended claims,along with the full scope of legal equivalents to which such claims areentitled.

The autonomic nervous system (ANS) regulates “involuntary” organs, whilethe contraction of voluntary (skeletal) muscles is controlled by somaticmotor nerves. Examples of involuntary organs include respiratory anddigestive organs, and also include blood vessels and the heart. Often,the ANS functions in an involuntary, reflexive manner to regulateglands, to regulate muscles in the skin, eye, stomach, intestines andbladder, and to regulate cardiac muscle and the muscles around bloodvessels, for example.

The ANS includes the sympathetic nervous system and the parasympatheticnervous system. The sympathetic nervous system is affiliated with stressand the “fight or flight response” to emergencies. Among other effects,the “fight or flight response” increases blood pressure and heart rateto increase skeletal muscle blood flow, and decreases digestion toprovide the energy for “fighting or fleeing.” The parasympatheticnervous system is affiliated with relaxation and the “rest and digestresponse” which, among other effects, decreases blood pressure and heartrate, and increases digestion to conserve energy. The ANS maintainsnormal internal function and works with the somatic nervous system.Afferent neurons convey impulses towards the central nervous system(CNS), and efferent neurons convey impulses away from the CNS.

Stimulating the sympathetic and parasympathetic nervous systems cancause heart rate, blood pressure and other physiological responses. Forexample, stimulating the sympathetic nervous system dilates the pupil,reduces saliva and mucus production, relaxes the bronchial muscle,reduces the successive waves of involuntary contraction (peristalsis) ofthe stomach and the motility of the stomach, increases the conversion ofglycogen to glucose by the liver, decreases urine secretion by thekidneys, and relaxes the wall and closes the sphincter of the bladder.Stimulating the parasympathetic nervous system (inhibiting thesympathetic nervous system) constricts the pupil, increases saliva andmucus production, contracts the bronchial muscle, increases secretionsand motility in the stomach and large intestine, increases digestion inthe small intestine, increases urine secretion, and contracts the walland relaxes the sphincter of the bladder. The functions associated withthe sympathetic and parasympathetic nervous systems are many and can becomplexly integrated with each other.

A reduction in parasympathetic nerve activity contributes to thedevelopment and progression of a variety of cardiovascular diseases.Some embodiments of the present subject matter can be used toprophylactically or therapeutically treat various cardiovasculardiseases by modulating autonomic tone. Neural stimulation to treatcardiovascular diseases is referred to herein as neurocardiac therapy(NCT). Vagal stimulation used to treat cardiovascular diseases may betermed either vagal stimulation therapy (VST) or NCT. However, VST maybe delivered for non-cardiovascular diseases, and NCT may be deliveredby stimulating a nerve other than the vagal nerve. Examples ofcardiovascular diseases or conditions that may be treated using VSTinclude hypertension, HF, and cardiac remodeling. These conditions arebriefly described below.

Hypertension is a cause of heart disease and other related cardiacco-morbidities. Hypertension occurs when blood vessels constrict. As aresult, the heart works harder to maintain flow at a higher bloodpressure, which can contribute to HF. Hypertension generally relates tohigh blood pressure, such as a transitory or sustained elevation ofsystemic arterial blood pressure to a level that is likely to inducecardiovascular damage or other adverse consequences. Hypertension hasbeen defined as a systolic blood pressure above 140 mm Hg or a diastolicblood pressure above 90 mm Hg. Consequences of uncontrolled hypertensioninclude, but are not limited to, retinal vascular disease and stroke,left ventricular hypertrophy and failure, myocardial infarction,dissecting aneurysm, and renovascular disease. A large segment of thegeneral population, as well as a large segment of patients implantedwith pacemakers or defibrillators, suffer from hypertension. The longterm mortality as well as the quality of life can be improved for thispopulation if blood pressure and hypertension can be reduced. Manypatients who suffer from hypertension do not respond to treatment, suchas treatments related to lifestyle changes and hypertension drugs.

HF refers to a clinical syndrome in which cardiac function causes abelow normal cardiac output that can fall below a level adequate to meetthe metabolic demand of peripheral tissues. HF may present itself ascongestive heart failure (CHF) due to the accompanying venous andpulmonary congestion. HF can be due to a variety of etiologies such asischemic heart disease. HF patients have impaired autonomic balance,which is associated with LV dysfunction and increased mortality.

Cardiac remodeling refers to a complex remodeling process of theventricles that involves structural, biochemical, neurohormonal, andelectrophysiologic factors, which can result following a myocardialinfarction (MI) or other cause of decreased cardiac output. Ventricularremodeling is triggered by a physiological compensatory mechanism thatacts to increase cardiac output due to so-called backward failure whichincreases the diastolic filling pressure of the ventricles and therebyincreases the so-called preload (i.e., the degree to which theventricles are stretched by the volume of blood in the ventricles at theend of diastole). An increase in preload causes an increase in strokevolume during systole, a phenomena known as the Frank-Starlingprinciple. When the ventricles are stretched due to the increasedpreload over a period of time, however, the ventricles become dilated.The enlargement of the ventricular volume causes increased ventricularwall stress at a given systolic pressure. Along with the increasedpressure-volume work done by the ventricle, this acts as a stimulus forhypertrophy of the ventricular myocardium. The disadvantage ofdilatation is the extra workload imposed on normal, residual myocardiumand the increase in wall tension (Laplace's Law) which represent thestimulus for hypertrophy. If hypertrophy is not adequate to matchincreased tension, a vicious cycle ensues which causes further andprogressive dilatation. As the heart begins to dilate, afferentbaroreceptor and cardiopulmonary receptor signals are sent to thevasomotor central nervous system control center, which responds withhormonal secretion and sympathetic discharge. The combination ofhemodynamic, sympathetic nervous system and hormonal alterations (suchas presence or absence of angiotensin converting enzyme (ACE) activity)account for the deleterious alterations in cell structure involved inventricular remodeling. The sustained stresses causing hypertrophyinduce apoptosis (i.e., programmed cell death) of cardiac muscle cellsand eventual wall thinning which causes further deterioration in cardiacfunction. Thus, although ventricular dilation and hypertrophy may atfirst be compensatory and increase cardiac output, the processesultimately result in both systolic and diastolic dysfunction. It hasbeen shown that the extent of ventricular remodeling is positivelycorrelated with increased mortality in post-MI and heart failurepatients.

Nerve cuffs may be used to stimulate the vagus nerve. Transvascularlystimulating the vagus nerve using electrodes in a blood vessel such asthe internal jugular vein is less invasive. Another less invasive meansfor stimulating the vagus nerve includes stimulating the vagus nerveusing electrodes placed proximate to the nerve within the carotidsheath. Verifying vagus nerve capture is desirable, particularly innon-cuff electrode arrangements. Verifying vagus nerve capture may alsobe relevant for automatic titration in both cuff and non-cuff electrodearrangements.

A branch of the vagus nerve is the recurrent laryngeal nerve, whichinnervates the laryngeal muscles. The vagus nerve is stimulated at astimulation site more cranial than the position where the recurrentlaryngeal nerve branches off of the vagus nerve. Stimulation thatcaptures the vagus nerve at this stimulation site enhances efferentvagal nerve traffic from this position, propagating action potentialsthrough the recurrent laryngeal nerve and causing laryngeal muscleactivation. Various embodiments of the present subject matter delivervagal stimulation to enhance efferent vagal nerve traffic, and detectactivation of the laryngeal muscles to provide feedback to a physicianduring the implantation procedure, to provide feedback to a physicianduring physician follow-ups, or to provide feedback for auto-titrationroutines intermittently performed in an implanted device.

The present subject matter generally refers to therapeutic stimulationof the vagus nerve. VST may include stimulation to increase vagus nervetraffic, stimulation to block or reduce vagus nerve traffic,unidirectional stimulation of the vagus nerve (e.g. stimulation thatsignificantly affects nerve traffic in the afferent direction but notthe efferent direction, or stimulation that significantly affects nervetraffic in the efferent direction but not the afferent direction), orstimulation that is non-unidirectional (e.g. stimulation thatsignificantly affects nerve traffic in both the afferent and efferentdirection). Therefore, the VST delivered from the stimulation electrodesfor the therapy may enhance efferent vagal nerve traffic after vagusnerve capture is verified or the therapy is titrated. However, thepresent subject matter may be used to verify vagus nerve capture, andthen provide a VST that does not enhance efferent vagal nerve activity.For example, the device may be configured to block efferent vagal nerveactivity or to deliver VST to unidirectionally enhance afferent vagusnerve activity after vagus nerve capture is verified. The parametersused to verify vagus nerve capture can be used to determine theappropriate VST parameters, whether the VST is configured to increaseafferent or efferent nerve traffic either unidirectionally ornon-unidirectionally, or whether the VST is configured to block ordecrease efferent nerve traffic, afferent nerve traffic or both efferentand afferent nerve traffic.

The vagus nerve is a complex physiological structure with many neuralpathways that are recruited at different stimulation thresholds. Variousphysiological responses to vagal stimulation are associated with variousthresholds of VST intensity. For example, FIG. 1 illustrates increasingVST intensity from the left side to the right side of the figure, andfurther illustrates intensity thresholds that elicit variousphysiological responses to VST. VST causes a physiological response “A”at a lower intensity than an intensity at which VST causes aphysiological response “B”, which occurs at a lower VST intensity thanan intensity at which VST causes a physiological response “C”. Statedanother way, VST triggers response “A” after reaching a certain level,triggers response “B” along with response “A” after reaching a higherintensity, and triggers response “C” along with responses “A” and “B”after reaching an even higher intensity.

Physiological responses at lower VST intensities havetherapeutically-effective results for cardiovascular diseases such asHF. Lower VST intensities may also have therapeutically-effectiveresults for other diseases. These responses mediate or provide pathwaysfor these therapies. Examples of such responses that are beneficial forHF at the lower VST intensities include anti-inflammation,anti-sympathetic, and anti-apoptosis responses, and an increased nitricoxide (NO). Physiological responses at the higher VST intensities maynot be desirable. Examples of responses to higher VST intensities thatmay reduce the ability of the patient to tolerate VST include, but arenot limited to, reduced heart rate, prolonged AV conduction,vasodilation, and coughing. At least some of these responses may bedesirable for some therapies but not desirable for other therapies. Byway of example and not limitation, VST that reduces heart rate and orthat prolongs AV conduction may be desirable to treat somecardiovascular diseases, but may not be desirable for othercardiovascular diseases. The intensity of the VST can be adjusted byadjusting parameter(s) of the stimulation signal. For example, theamplitude of the signal (e.g. current or voltage) can be increased toincrease the intensity of the signal. Other stimulation parameter(s) canbe adjusted as an alternative to or in addition to amplitude. Forexample, stimulation intensity can vary with the frequency of thestimulation signal (e.g. a frequency of stimulation pulses), astimulation burst frequency (e.g. a plurality of bursts delivered at aburst frequency for initiating bursts where each burst includes aplurality of pulses), a pulse width and/or a duty cycle. Typical vagalnerve stimulation may have a signal amplitude of above 0.1-10 mA and afrequency of about 1-50 Hz.

FIG. 2 illustrates increasing VST intensity from the left side to theright side of the figure, and further illustrates an intensity thresholdfor a laryngeal vibration response that can be used to determine captureand that can further be used as a lower boundary or to determine thelower boundary. A vagus nerve capture threshold can be set by confirmingcapture of the vagus nerve using laryngeal vibration. The stimulationparameters may be set based on the stimulation parameters that causedthe laryngeal vibrations. For example, if the amplitude of thestimulation signal is increased to increase the VST intensity and if 1.0mA caused laryngeal vibrations, then the pacing amplitude may be set toan offset value (x mA) above the laryngeal vibration threshold amplitude(e.g. 1 mA+x mA) or as a factor of the laryngeal vibration threshold(e.g. 1 mA*factor). Additionally, some embodiments may place an upperboundary on the VST. The upper boundary may be based on a detectedundesired response to the stimulation, such as cough or undesired musclestimulation.

Embodiments of the present subject matter use electromyogram (EMG)sensor(s) to detect activity of the laryngeal muscles. Some embodimentsuse multiple sensor strategies, along with the EMG sensor(s), to confirmvagal nerve stimulation. For example, an accelerometer could be used inthe same time window and operating at a different bandwidth.

FIG. 3 generally illustrates a right vagus nerve 100 and a recurrentlaryngeal nerve 101 branching off of the right vagus nerve to innervatethe laryngeal muscles 102 near the trachea 103. There is also a leftvagus nerve (not illustrated) and a recurrent laryngeal nerve (notillustrated) branching off of the left vagus nerve to innervate thelaryngeal muscles near the trachea. The ability to verify capture of avagus nerve through EMG sensing of activity in laryngeal muscles may beused with right and/or left vagus nerve stimulation. The recurrentlaryngeal nerve branches off the vagus nerve at a position caudal to thelaryngeal muscles, and then loops back cranially to innervate thelaryngeal muscles. This loop is a relatively lengthy neural pathway thatprovides latency between the time of a vagus nerve stimulation pulse andthe time of the activation of the laryngeal muscles. Because of thislatency, the laryngeal activation can be measured by EMG sensors afterthe pulse without being blunted by the stimulation artifact. Further,the loop provides options for adjusting the distance between the vagusnerve stimulation site and the laryngeal muscles. For example, in theembodiment illustrated in FIG. 3, the stimulation electrodes may beplaced to stimulate the vagus nerve at stimulation site 104 relativelynear the point 105 where the recurrent laryngeal nerve branches off thevagus nerve, and the EMG sensor(s) can be positioned along the vagusnerve at EMG sensing site 106 proximate to the laryngeal muscles toimprove detection of activity in the laryngeal muscles and reduce thepotential of interference from stimulation pulses. The stimulationelectrodes and EMG sensor(s) may be on the same lead.

The vagus nerve includes A-fibers, B-fibers, and C-fibers. A-fibers areabout 5-20 μm in diameter and conduct neural responses at a rate ofapproximately 0.08-0.33 ms/cm. B-fibers are about 1-5 μm in diameter andconduct neural responses at a rate of approximately 0.33-1.67 ms/cm.C-fibers are about 0.2-1.5 μm in diameter and conduct neural responsesat a rate of approximately 8.16-22.36 ms/cm. U.S. application Ser. No.13/156,879, filed Jun. 9, 2011 and entitled “Methods and Apparatus forControlling Neurostimulation Using Evoked Responses” is incorporatedherein by reference in its entirety. The larger fibers have a lowerstimulation threshold than smaller fibers. Thus, the A-fibers have thelowest stimulation threshold. A-fibers of the vagus nerve are alsosomatic fibers, some of which branch off into the recurrent laryngealnerve that innervate the muscles of the larynx.

Assuming a 0.17 ms/cm conduction rate for a 10 μm A-fiber thatinnervates the muscles of the larynx and assuming 50-60 cm of traveldistance from the stimulated location of the vagus nerve into therecurrent laryngeal nerve and back up to the laryngeal muscles, themuscles of the larynx will activate about 8.33-10 ms after the vagusnerve is stimulated. Thus, the response of the laryngeal muscles tovagal nerve stimulation has a relatively long latency because of therelatively long travel distance. The actual distance from thestimulation site to the laryngeal muscles will depend on the location ofthe stimulation site and the specific anatomy of the patient. Forexample, taller people with longer necks may have longer recurrentlaryngeal nerves. Patient specific templates may be developed to accountfor the specific anatomical differences in the patient.

FIGS. 4A and 4B illustrate the latency of the laryngeal muscle activityto a vagus nerve pulse, comparing an ENG signal (FIG. 4A) to an EMGsignal (FIG. 4B). A vagus nerve pulse 107 occurs at Time 0. An evokedneural response 108, including both an A-fiber response and a B-fiberresponse, to the pulse is detected by vagus ENG sensors (top) and an EMGshowing the response of the laryngeal muscles to the pulse is detectedby EMG sensor(s). As illustrated, the activity of the laryngeal musclesis about 10 ms after the delivery of the vagus nerve pulse.

Some embodiments use multiple lead configurations and recording vectors.For example, some embodiments use a bipolar electrode arrangement usinga multi-polar lead such as a quad polar lead. Some embodiments use atripolar electrode arrangement using three electrodes on the lead, whichmay improve stimulation artifact control. Some embodiments use amonopolar electrode arrangement, where an electrode on the pulsegenerator and an electrode on the lead provide the stimulation vector.Some embodiments deliver bilateral vagal nerve stimulation, using aright lead positioned to stimulate the right vagus nerve and a left leadpositioned to stimulate the left vagus nerve. When the right vagus nerveis stimulated, the left lead is used to sense laryngeal activity; andwhen the left vagus nerve is stimulated, the right lead is used to senselaryngeal activity.

FIGS. 5-8 illustrate various embodiments for positioning electrodes tostimulate the vagus nerve and record activity of laryngeal muscles usingan EMG signal. FIG. 5 illustrates a vagus nerve 100 and a recurrentlaryngeal nerve 101 branching off of the vagus nerve to innervate thelaryngeal muscles 102 near the trachea 103, and further illustrate anerve cuff embodiment. A lead 110 is attached to the vagus nerve 100 bya nerve cuff 111, and the nerve cuff includes electrodes used tostimulate the vagus nerve and to record EMG signals representingactivity of the laryngeal muscles. If the vagus nerve is being captured,the pulses from the nerve cuff 111 stimulate efferent nerve activity inthe vagal nerve through the recurrent nerve to the laryngeal muscles. Insome embodiments, the neural stimulation electrodes are used to recordthe EMG signals. The same electrodes used to stimulate the vagus nervemay be used to record EMG activity. Some embodiments implement anautocapture routine that blank the sensing during the stimulation andthen sense for an EMG artifact caused by an evoked response of thelaryngeal muscles to the vagus nerve stimulation. In some embodiments,the nerve cuff includes a first set of electrodes used to stimulate thevagus nerve and includes a second set of electrodes used to record theEMG signal. In some embodiments, the first and second sets of electrodesare exclusive of each other. In some embodiments, the first and secondsets of electrodes include at least one common electrode used to bothstimulate the vagus nerve and record EMG activity.

FIG. 6A illustrates a nerve cuff embodiment with recording electrodes112A and with stimulation electrodes 113A positioned in a more caudalposition closer to a position 105 where the recurrent laryngeal nervebranches from the vagus nerve 100. The position of the stimulationelectrodes 113A at the stimulation site is cranial to the location wherethe recurrent laryngeal nerve branches from the vagus nerve. Thestimulation electrodes 113A and the recording electrodes 112A are on alead 110A. The illustrated stimulation electrodes 113A are part of anerve cuff. The recording electrodes 112A are on a distal end of thelead 110A. If the vagus nerve is being captured, the pulses from thenerve cuff stimulate efferent nerve activity in the vagal nerve throughthe recurrent nerve to the laryngeal muscles, and the recordingelectrodes are capable of detecting activity in the laryngeal musclescaused by the vagus nerve pulses. The lower (more caudal) position ofthe stimulation electrodes places more distance between the stimulationelectrodes and recording electrodes, which is believed to reduce a riskof interference.

FIG. 6B illustrates a nerve cuff embodiment with recording electrodes112B and with stimulation electrodes 113B positioned in a more caudalposition closer to a position 105 where the recurrent laryngeal nervebranches from the vagus nerve. The position of the stimulationelectrodes 113B at the stimulation site is cranial to the location wherethe recurrent laryngeal nerve branches from the vagus nerve. Thestimulation electrodes 113B and the recording electrodes 112B are on alead 110B. The illustrated stimulation electrodes 113A are part of anerve cuff. The stimulation electrodes 113B are on a distal end of thelead 110B. If the vagus nerve is being captured, the pulses from thenerve cuff stimulate efferent nerve activity in the vagal nerve throughthe recurrent nerve to the laryngeal muscles, and the recordingelectrodes are capable of detecting activity in the laryngeal musclescaused by the vagus nerve pulses. The lower (more caudal) position ofthe stimulation electrodes places more distance between the stimulationelectrodes and recording electrodes, which is believed to reduce a riskof interference.

FIG. 7 illustrates an intrasheath lead embodiment, in which thestimulation and recording electrodes are placed within a carotid sheath116 proximate to the vagus nerve. The carotid sheath 116 refers to thefibrous connective tissue that surrounds the carotid artery and relatedstructures in the neck. The carotid sheath 116 contains the carotidarteries, the internal jugular vein, and the vagus nerve. Theglossopharyngeal nerve and accessory nerve courses in the upper part ofthe carotid sheath 116, and the hypoglossal nerve passes through or nearthe carotid sheath 116. The internal jugular vein 114, the vagus nerve100 and the carotid artery 115 are physiological structures found withinthe carotid sheath 116. The recording electrodes 117 are placed withinthe carotid sheath 116 approximately near the level of the laryngealmuscles, and the stimulation electrodes 118 are placed more caudallynear the vagus nerve but still cranial to the location where therecurrent laryngeal nerve branches from the vagus nerve. If the vagusnerve is being captured, the pulses from the nerve cuff stimulateefferent nerve activity in the vagal nerve through the recurrent nerveto the laryngeal muscles, and the recording electrodes are capable ofdetecting activity in the laryngeal muscles. The recording electrodesand stimulation electrodes are on the same lead and are fed into thecarotid sheath with the lead.

FIG. 8 illustrates an intravascular embodiment, in which the stimulationand recording electrodes are placed within an internal jugular veinproximate to the vagus nerve. The recording electrodes 117 are placedwithin the internal jugular vein 114 approximately near the level of thelaryngeal muscles 103, and the stimulation electrodes 118 are placedmore caudally near the vagus nerve 100 but still cranial to the location105 where the recurrent laryngeal nerve 101 branches from the vagusnerve 100. If capturing the vagus nerve, the pulses from the nerve cuffstimulate efferent nerve activity in the vagal nerve through therecurrent nerve to the laryngeal muscles, and the recording electrodesare capable of detecting activity in the laryngeal muscles. The lead isfixed within the vessel using an anchoring system, such as an expandablestent-like device(s) 119. The anchoring system can function to maintainthe position of the electrodes against a vessel wall proximate to thevagus nerve, and at the desired cervical region to stimulate the vagusnerve and sense the resulting activity of the laryngeal muscles.

FIGS. 9-10 illustrate results of an experiment in which the vagus nervewas stimulated, an ENG signal reflecting vagal nerve traffic wasrecorded using a nerve cuff around the vagus nerve, and EMG signals oflaryngeal muscle activity were recorded using a needle EMG sensorpercutaneously placed on the larynx muscles and a lead EMG sensorimplanted in the carotid sheath next to the vagus nerve. Stimulation andlead EMG recordings were done from the same multi-polar lead implantedin the carotid sheath right next to the vagus nerve. The ENG and EMGsignals show a representation of the pulse 120 and a response 121 to thepulse 120. FIG. 9 illustrates three neural stimulation pulses, and FIG.10 is a closer view of a single pulse. As illustrated in the figures,the EMG signals are related to the ENG signal, albeit delayed by thelatency that it takes to propagate action potentials through the vagusand recurrent laryngeal nerve, indicating that the EMG of laryngealmuscle activity is a reliable indicator of vagus nerve capture.Furthermore, the lead-based EMG sensor corresponds closely to the needleEMG sensor, indicating that the lead-based EMG sensor is also a reliableindicator of the laryngeal nerve activity and thus a reliable indicatorof vagus nerve capture.

A capacitive double layer of charge forms when stimulus pulse isdelivered after-potential or polarization. A recharge pulse can bedelivered to remove this charge. However, the recording electrodes areused to sense an EMG signal from the laryngeal muscles in a sensingwindow approximately 10 ms after the vagus nerve stimulation pulse. Theexact timing of the sensing window may depend on patient-specificanatomy and the position of the stimulation electrodes. Variousembodiments provide a recharge after a stimulation pulse withoutinterfering with the sensing of the laryngeal muscles within the sensingwindow.

According to an embodiment, an active recharge phase is used to completethe recharge before a sensing window for sensing laryngeal activityusing the EMG sensors. For example, a cathodic stimulus phase isfollowed by an active anodic stimulus recharge phase that completesbefore the sensing window. In an embodiment, the recharge pulse is equalin amplitude (I₁≈I₂) and pulse width (PW₁≈PW₂) to the cathodic stimulusphase, but opposite polarity, such as is generally illustrated in FIG.11A.

According to an embodiment, a passive recharge phase is stopped toprovide a window for sensing laryngeal activity using the EMG sensors,and then resumed after the window to finish the recharge phase. Forexample, a cathodic stimulus phase is followed by a passive anodicstimulate recharge phase. A passive recharge phase is generallyillustrated in FIG. 11B by the exponential waveform following thestimulation pulse PW and a delay. The recharge phase is stopped, ifnecessary, to provide a sensing window for a period of time when thelaryngeal activity is expected. After the sensing window is completed,the passive anodic stimulus recharge phase is resumed and completed.

According to an embodiment, the EMG sensors are cable of sensingamplitudes within an approximate range of 0 to 500 μV, and have abandwidth with an approximate range of 10-200 Hz. However, the presentsubject matter is not limited to a particular range of amplitudes orbandwidth. The detection can be performed by comparing parameter(s) fromthe sensed signal to a template. In some embodiments, the implantingphysician creates the template after implanting the device. In someembodiments, a physician creates the template during a follow-up visit.In creating the template, the EMG signal is monitored for a signaldeflection to flag the event as a vagal nerve capture event. A number ofvagal nerve capture events can be averaged or otherwise processed toprovide the template, and to provide the sensing window timing forsensing laryngeal muscle activity after a vagus stimulation pulse.Signal averaging strategies can be used to demonstrate that the majorityof pulses capture the vagus nerve. It is not necessary to demonstratethat an isolated pulse produced detectable activity in the laryngealmuscles.

According to some embodiment the sense amplifiers are blanked during thestimulus pulse. The gain and filter characteristics of the amplifiersare appropriate to detect the small signal representing the EMG ofactive laryngeal muscles. Some embodiments calibrate the sensors foreach patient as amplitudes and timing may vary slightly because ofimplant location, neck length, and the like.

Signal processing is expected to be able to distinguish activation oflaryngeal muscles from other muscle activity (e.g. neck motion).However, some embodiments of the laryngeal activity sensing areperformed when the patient is still to prevent interference from othermuscles. Patient movement is not an issue during an implantationprocedure, and the patient may be instructed to lie still during afollow-up exam. In an implanted device embodiment configured toautomatically perform the capture detection, the device may beconfigured to sense activity or motion or voice, and to disable thecapture detection routine or otherwise provide context for recording EMGsignals when the activity or motion or voice is above a threshold level.

Various embodiments use capture detection to augment a stimulation dosein the ambulatory setting. For example, a threshold capture routine canbe performed for the ambulatory patient. The routine may be triggered bya physician, by a patient, or automatically based on a schedule, aperiod of time, or a sensed activity or event. The threshold may changeover time because of lead migration, changes in the electrode-tissueinterface, and neurological habituation to the stimulation signal, forexample. The dose of the stimulation can be increased to account for thechange in the stimulation threshold.

Various embodiments associate EMG strength to B-fiber capture andtherapy delivery, such as described in U.S. application Ser. No.13/156,879, filed Jun. 9, 2011 and entitled “Methods and Apparatus forControlling Neurostimulation Using Evoked Responses”, which isincorporated herein by reference in its entirety. It is believed that anapproximately constant relationship can be identified between thestimulation threshold for capturing the A-fibers and the stimulationthreshold for effectively modulating a target physiological functionthrough capturing the B-fibers. The stimulation intensity is a minimumstimulation intensity required to activate laryngeal muscles. Once aninitial stimulation threshold providing for the initial evoked muscularresponse is determined, the stimulation intensity for therapeuticallystimulating B-fibers is set to a level that is determined by using theinitial stimulation threshold and the identified approximately constantrelationship. The initial evoked muscular response is the evokedmuscular responses that start to become detectable as the stimulationintensity increases from a low initial level. The initial stimulationthreshold is the stimulation intensity that produces the initial evokedmuscular response. In one embodiment, the approximately constantrelationship is quantitatively established using a patient population.The stimulation intensity for a vagus nerve stimulation therapy appliedto the patient is then set using the initial stimulation threshold andthe established approximately constant relationship.

The titration and capture detection routines can be triggered manuallyby a physician, triggered manually by a patient, or triggeredautomatically according to a programmed schedule or according to a timeinterval or according to a detected event. A titration can be triggeredif it is determined that the stimulation is not capturing the vagusnerve.

To confirm capture of the vagus nerve, a device embodiment switchesbetween normal and titration modes and switches between normal andconfirmation modes. Titration has a higher priority than confirmationwhich has higher priority than normal mode. Performingtitration/confirmation can be gated or aborted or blocked or delayed bya detected event or sensed context. For example, titration/confirmationcan be gated or aborted or blocked or delayed by detecting anarrhythmia, a posture sensor value, a sleep sensor value, an activitysensor value, detected apnea or detected irregular breathing.

Titration, as used herein, refers to the process of adjusting the doseof the stimulation, ultimately to a level that is therapeutically orprophylactically effective. The titration procedure may occur during animplantation procedure, or during a follow-up clinical visit, or while apatient is ambulatory away from the clinical setting. The titration maybe physician-controlled or automatically-controlled based on deviceprogramming. The dose includes an amount or intensity of the neuralstimulation at a given time frame, and also includes the number of timesthe neural stimulation is delivered over a period of time. The intensityof the neural stimulation may be adjusted by adjusting parameters suchas amplitude, duty cycle, duration, and or frequency of the neuralstimulation, or the number of neural stimulation events that occur overa period of time.

FIG. 12 illustrates a representation of intermittent neural stimulation(INS). The figure diagrammatically shows the time-course of a neuralstimulation that alternates between intervals of stimulation being ON,when one stimulation pulse or a set of grouped stimulation pulses (i.e.,a burst 122) is delivered, and intervals of stimulation being OFF, whenno stimulation pulses are delivered. Thus, for example, some embodimentsdeliver a plurality of monophasic or biphasic pulses within a neuralstimulation burst illustrated in FIG. 12. Pulses delivered within aburst 122 may be delivered at a pulse frequency. These pulses also havean amplitude. Both the pulse frequency and the pulse amplitude affectthe dose of the neural stimulation therapy. The duration of thestimulation ON interval is sometimes referred to as the stimulationduration or burst duration. The burst duration also affects the dose ofthe neural stimulation therapy. The start of a stimulation ON intervalis a temporal reference point NS Event. The time interval betweensuccessive NS Events is the INS Interval, which is sometimes referred toas the stimulation period or burst period 123. The burst period 123 orthe number of neural stimulation events that occur over a time periodalso affect the dose of the neural stimulation. For an application ofneural stimulation to be intermittent, the stimulation duration (i.e.,ON interval) is less than the stimulation period (i.e., INS Interval)when the neural stimulation is being applied. The duration of the OFFintervals of INS are determined by the durations of the ON interval andthe INS Interval. The duration of the ON interval relative to the INSInterval (e.g., expressed as a ratio) is sometimes referred to as theduty cycle of the INS.

A physician or clinician may control the adjustment of one or moreneural stimulation parameters to control the stimulation intensity. Forexample, during an implantation procedure in which stimulationelectrodes are implanted near a vagus nerve, the physician or clinicianmay adjust stimulation parameter(s) to adjust the stimulation intensityto appropriately position the electrodes and program the stimulation toprovide threshold stimulation of the neural target that provides adesired physiological effect. A desired physiological effect, accordingto various embodiments, is laryngeal vibrations caused by thestimulation of the vagus nerve cranially to the position where thelaryngeal nerve branches from the vagus nerve. The physician orclinician may re-program an implantable neural stimulator during afollow-up visit, to account for migration of the electrodes, changes inimpedance in the electrode/tissue interface, and the like. During thefollow-up visit, the physician or clinician may control the adjustmentof one or more neural stimulation parameters to control the stimulationintensity to determine a neural stimulation intensity that provides thedesired physiological response. The titration routine can be anautomatic process for an implantable neural stimulation device implantedin an ambulatory patient, such as generally illustrated in FIG. 14. Theautomatic titration routine can be manually triggered by a signal from apatient or by the physician or clinician. The automatic titrationroutine can be automatically triggered by a programming schedule or by asensed event.

FIG. 13 illustrates a memory 124, according to various embodiments, thatincludes instructions 125, operable on by the stimulation controlcircuitry, to control an up-titration routine by progressively steppingup through defined parameter sets (e.g. parameter set 1 throughparameter set N), where each set incrementally changes (increases ordecreases) the stimulation dose or intensity of the stimulation therapy.This memory may be illustrated as part of a therapy titration/adjustmentmodule 126 in FIG. 14 which may function as a parameter adjusterdiscussed below. The memory may include a plurality of neuralstimulation parameter sets, where each set includes a unique combinationof parameter values for the neural stimulation and wherein each uniquecombination of parameter values is defined to provide neural stimulationtherapy at an intensity level. The instructions include instructions forstepping through the plurality of neural stimulation parameter setsaccording to a schedule to change (increase or decrease) the intensityof the therapy until the therapy is at the desired long term intensity.Various embodiments provide a neural stimulation routine thatautomatically finds the desirable combination of therapy parameters(e.g. amplitude, pulse width, duty cycle) that provides a desiredtherapy intensity level.

FIG. 14 illustrates an embodiment of a therapy titration module 126,which may also be referred to as a therapy adjustment module. Accordingto various embodiments, the stimulation control circuit is adapted toset or adjust any one or any combination of stimulation features 127.Examples of stimulation features include the amplitude, pulse width,duty cycle and frequency of the stimulation signal. Some embodiments ofthe stimulation output circuit are adapted to generate a stimulationsignal with a predetermined amplitude, pulse width, duty cycle andfrequency and are further adapted to respond to a control signal fromthe controller to modify at least one of the amplitude, pulse width,duty cycle and frequency.

The therapy titration module 126, also referred to as a therapyadjustment module, can be programmed to change an electrode set orelectrode configuration or to change stimulation sites 128, such aschanging the stimulation electrodes used for a neural target or changingthe neural targets for the neural stimulation. For example, differentelectrodes can be used to stimulate a neural target, and differentelectrodes can be used to stimulate different neural targets. Adesirably low stimulation threshold for a neural target may bedetermined using different electrode sets/configurations for stimulatingthat neural target. Different neural targets can include differentneural pathways such as the right and left vagus nerves. Differentneural targets may include different positions along a neural pathway(e.g. more caudal or more cranial targets along a cervical vagus nerve).The neural stimulation delivered to confirm capture of the vagus nervemay be but need not be the same stimulation as delivered during the VST.For example, the VST may include stimulation to stimulate neural trafficor stimulation to inhibit neural traffic. Thus, stimulation to evoke asympathetic response can involve inhibition of the parasympathetictraffic in the vagus nerve, and stimulation to evoke a parasympatheticresponse can involve stimulation of the parasympathetic traffic in thevagus nerve.

The therapy titration module 126 can be programmed to change stimulationvectors 129. Vectors can include stimulation vectors between electrodes,or stimulation vectors for transducers. For example, the stimulationvector between two electrodes can be reversed. More complicatedcombinations of electrodes can be used to provide more potentialstimulation vectors between or among electrodes.

The therapy titration module 126 can be programmed to control the neuralstimulation according to stimulation instructions, such as a stimulationroutine or schedule 130, stored in memory. Neural stimulation can bedelivered in a stimulation burst, which is a train of stimulation pulsesat a predetermined frequency. Stimulation bursts can be characterized byburst durations and burst intervals. A burst duration is the length oftime that a burst lasts. A burst interval can be identified by the timebetween the start of successive bursts. A programmed pattern of burstscan include any combination of burst durations and burst intervals. Asimple burst pattern with one burst duration and burst interval cancontinue periodically for a programmed period or can follow a morecomplicated schedule. The programmed pattern of bursts can be morecomplicated, composed of multiple burst durations and burst intervalsequences. The programmed pattern of bursts can be characterized by aduty cycle, which refers to a repeating cycle of neural stimulation ONfor a fixed time and neural stimulation OFF for a fixed time. Duty cycleis specified by the ON time and the cycle time, and thus can have unitsof ON time/cycle time. According to some embodiments, the controlcircuit controls the neural stimulation generated by the stimulationcircuitry by initiating each pulse of the stimulation signal. In someembodiments, the stimulation control circuit initiates a stimulationsignal pulse train, where the stimulation signal responds to a commandfrom the controller circuitry by generating a train of pulses at apredetermined frequency and burst duration. The predetermined frequencyand burst duration of the pulse train can be programmable. The patternof pulses in the pulse train can be a simple burst pattern with oneburst duration and burst interval or can follow a more complicated burstpattern with multiple burst durations and burst intervals. In someembodiments, the stimulation control circuit controls the stimulationoutput circuit to initiate a neural stimulation session and to terminatethe neural stimulation session. The burst duration of the neuralstimulation session under the control of the control circuit can beprogrammable. The controller may also terminate a neural stimulationsession in response to an interrupt signal, such as may be generated byone or more sensed parameters or any other condition where it isdetermined to be desirable to stop neural stimulation.

A device may include a programmed therapy schedule or routine stored inmemory and may further include a clock or timer which can be used toexecute the programmable stimulation schedule. For example, a physiciancan program a daily/weekly schedule of therapy based on the time of day.A stimulation session can begin at a first programmed time, and can endat a second programmed time. Various embodiments initiate and/orterminate a stimulation session based on a signal triggered by a user.Various embodiments use sensed data to enable and/or disable astimulation session.

According to various embodiments, the stimulation schedule refers to thetime intervals or period when the neural stimulation therapy isdelivered. A schedule can be defined by a start time and an end time, ora start time and a duration. Various schedules deliver therapyperiodically. By way of example and not limitation, a device can beprogrammed with a therapy schedule to deliver therapy from midnight to 2AM every day, or to deliver therapy for one hour every six hours, or todeliver therapy for two hours per day, or according to a morecomplicated timetable. Various device embodiments apply the therapyaccording to the programmed schedule contingent on enabling conditions,such as sensed exercise periods, patient rest or sleep, a particularposition/posture, low heart rate levels, and the like. For example, thestimulation can be synchronized to the cardiac cycle based on detectedevents that enable the stimulation. The therapy schedule can alsospecify how the stimulation is delivered.

Some embodiments are configured to change a ramp-up time for increasingone or more stimulation parameters from OFF to a programmed intensity atthe start of the ON portion. Patients may tolerate higher stimulationlevels if there is not an abrupt change at the start of the duty cycle.The parameter increased during this ramp-up time may be amplitude, forexample, or other parameter or other combination of parameters thataffect the intensity of the stimulation.

FIG. 15 illustrates an embodiment for titrating stimulation parameters.Normal VST is delivered at 131. At 132, it is determined whether it istime to titrate or verify capture. This timing may be based on aschedule, a patient-controlled trigger, a physician-controlled trigger,or a sensed event. If it is determined that it is time to titrate orverify capture, the therapy parameters are disabled at 133 and thetitration is initiated at 134. The titration may be automatic orsemi-automatic. A titration routine is performed at 135. At 136, it isdetermined if titration is done. If titration is done, the therapyparameters are enabled at 137. Otherwise, the titration routinecontinues at 135 until the titration is done.

FIG. 16 illustrates an embodiment, by way of example and not limitation,of an implantable medical device 138 with a device housing or can 139and a lead 140 extending from the can. The lead includes multiple polesthat can be used in various stimulation configurations includingunipolar and bipolar configurations. The lead may be an intravascularlead configured to be fed into position through the vasculature of thepatient. The lead may be a subcutaneous lead. The lead may be inside oroutside the carotid sheath, to provide electrode(s) either adjacent toor surrounding the vagus nerve. The lead includes at least one group ofelectrodes to provide the stimulation and recording. The illustratedlead includes two sets of electrodes (Group A and Group B). Each groupof electrodes includes one or more electrodes. In some embodiments, thedevice is configured to switch between different electrodeconfigurations to change stimulation and/or sensing vectors. One groupof electrode(s) is used to sense laryngeal muscle activity, and theother group of electrode(s) is used to stimulate the vagus nerve.However, the present subject matter is not limited to a particularnumber of electrodes or groupings of electrodes. In some embodiments,electrodes from different groups on the leads may be used to provide thedesired stimulation/sensing vectors. The can 139 may function as anelectrode. In some embodiments, more than one electrode may be on thecan 139.

FIG. 17 illustrates an embodiment of a routine for finding thresholdvalues for each of the electrode configurations. The illustrated routineincreases the intensity of the neural stimulation therapy over a periodof time. The intensity is increased in increments 140. In theillustrated embodiments, a threshold determination routine 141 isperformed to detect a lower boundary physiologic response to the neuralstimulation such as a laryngeal vibration response. In variousembodiments, a side effect detection routine 142 is performed to detectan upper boundary physiologic response (e.g. cough) to the neuralstimulation. Some embodiments decrease the intensity of the NCT therapyover a period of time to detect the desired or undesired physiologicresponses to the neural stimulation.

Various embodiments detect laryngeal vibration using electromyogramsensors. The laryngeal vibration is a desired physiological responsethat confirms vagal nerve capture. Some embodiments use sensors todetect an undesired response (e.g. cough or phrenic nerve capture). Thesensors may be part of an implantable device, such as an implantablenerve stimulator used to stimulate the target nerve. In some embodimentsthe sensors are part of a programmer/PSA (pacing system analyzer) orother external system. Some embodiments correlate the timing of theneural stimulation bursts to the timing of the physiological responsesto determine whether the physiological response is attributable to theNCT. Some embodiments use feedback from a patient or physician. Forexample, a clicker pad with a pain assessment or other scale can be usedto allow the patient to provide feedback as to whether the stimulationprovides cough or phrenic nerve capture or other undesired physiologicalresponse to the stimulation. The algorithm can be implemented in theprogrammer, or in the implantable device, or in an external deviceconfigured to communicate with the programmer and/or the implantabledevice such as in a patient management system.

Some embodiments repeat the algorithm periodically or intermittently,such as may be appropriate to account for lead migration and/or therapyoptimization. The system (e.g. device or programmer) may be programmedto initiate the algorithm automatically. In some embodiments, thepatient initiates the algorithm using an external device or a signal(e.g. magnet or wireless communication) with the implantable device. Insome embodiment the physician or clinician initiates the algorithm.

FIGS. 18-19 illustrate system embodiments adapted to provide VST, andare illustrated as bilateral systems that can stimulate both the leftand right vagus nerve. The leads can be used to sense EMG signalsrepresenting laryngeal muscle activity. Those of ordinary skill in theart will understand, upon reading and comprehending this disclosure,that systems can be designed to stimulate only the right vagus nerve,systems can be designed to stimulate only the left vagus nerve, andsystems can be designed to bilaterally stimulate both the right and leftvagus nerves. The systems can be designed to stimulate nerve traffic(providing a parasympathetic response when the vagus is stimulated), orto inhibit nerve traffic (providing a sympathetic response when thevagus is inhibited). Various embodiments deliver unidirectionalstimulation or selective stimulation of some of the nerve fibers in thenerve. FIGS. 18-19 illustrate the use of a lead to stimulate the vagusnerve. Wireless technology could be substituted for the leads, such thata leadless electrode is adapted to stimulate a vagus nerve and isfurther adapted to wirelessly communicate with an implantable system foruse in controlling the VST.

FIG. 18 illustrates a system embodiment in which an IMD 143 is placedsubcutaneously or submuscularly in a patient's chest with lead(s) 144positioned to stimulate a vagus nerve. According to various embodiments,neural stimulation lead(s) 144 are subcutaneously tunneled to a neuraltarget, and can have a nerve cuff electrode to stimulate the neuraltarget. Some vagus nerve stimulation lead embodiments areintravascularly fed into a vessel proximate to the neural target, anduse electrode(s) within the vessel to transvascularly stimulate theneural target. For example, some embodiments stimulate the vagus usingelectrode(s) positioned within the internal jugular vein. Otherembodiments deliver neural stimulation to the neural target from withinthe trachea, the laryngeal branches of the internal jugular vein, andthe subclavian vein. The neural targets can be stimulated using otherenergy waveforms, such as ultrasound and light energy waveforms. Someembodiments include leadless ECG electrodes 145, such as on the housingof the implantable device as shown in the illustrated system. These ECGelectrodes are capable of being used to detect heart rate, for example.FIG. 19 illustrates an IMD 143 placed subcutaneously or submuscularly ina patient's chest with lead(s) 146 positioned to provide a CRM therapyto a heart, and with lead(s) 144 positioned to stimulate and/or inhibitneural traffic at a vagus nerve, according to various embodiments.

FIG. 20 is a block diagram illustrating an embodiment of a vagus nervestimulation system 147. The illustrated system 147 includes stimulationelectrodes 148, a stimulation output circuit 149, an evoked responsesensor 150, a sensor processing circuit 151, an evoked responsedetection circuit 152, a control circuit 153, and a storage circuit 154.The stimulation electrodes 148 include one or more stimulationelectrodes to be placed in the patient's body in one or more locationssuitable for delivering neurostimulation pulses to activate a vagusnerve.

The evoked response sensor may include recording electrodes as discussedabove. The evoked response sensor 150 is to be placed in or on thepatient' body in a location suitable for sensing a physiological signalindicative of evoked responses being physiologic events evoked by theneurostimulation pulses. The evoked response sensor includes a laryngealactivity sensor to sense an evoked muscular response includingactivities of laryngeal muscle evoked by the neurostimulation pulses.The sensor processing circuit 151 processes the physiological signal inpreparation for detection of the evoked responses. The evoked responsedetection circuit 152 receives the processed physiological signal fromsensor processing circuit 151, detects the evoked responses using theprocessed physiological signal, and generates one or more responsesignals representative of the detected evoked responses. The one or moreresponse signals includes information about, for example, whether thevagus nerve is captured by the neurostimulation pulses and measuredcharacteristics of the evoked responses. The control circuit 153controls the delivery of the neurostimulation pulses using a stimulationintensity. The control circuit 153 includes a parameter adjustor 155 toadjust the stimulation intensity by adjusting one or more stimulationparameters (e.g. amplitude, pulse width, or duty cycle). In oneembodiment, the parameter adjustor adjusts the one or more stimulationparameters using the one or more response signals generated by theevoked response detection circuit 152. The storage circuit 154, whichmay be part of or separate from a memory that includes programmedinstructions for the device, stores the evoked responses in the form ofone or more waveforms of the evoked responses and the one or morecharacteristic parameters of the evoked responses. In one embodiment,the storage circuit 154 stores the stimulation intensity associated withdetected evoked responses. The circuit of system 147 can be programmedto perform the various functions discussed in this document.

FIG. 21 is a block diagram illustrating an embodiment of a vagus nervestimulation system 156 that includes stimulation electrodes 148,stimulation output circuit 149, evoked response sensor 150, sensorprocessing circuit 151, an evoked response detection circuit 152, acontrol circuit 153, and storage circuit 154.

The evoked response detection circuit 152 detects the evoked responsesusing the physiological signal and generates one or more responsesignals representative of the detected evoked responses. The evokedresponse detection circuit 152 includes a detection timer 156, acomparator 157, and a measurement module 158. The detection timer 156controls timing of detection of the evoked responses. Examples of suchtiming include initiation of the detection according to a specifiedschedule and one or more detection windows within which the evokedresponses are expected to be detected. The comparator 157 detects theevoked responses by comparing the physiological signal to one or moredetection thresholds. In one embodiment, the comparator 157 detects theevoked responses by comparing the physiological signal to one or moredetection thresholds during the one or more detection windows. Themeasurement module 158 measures one or more characteristic parameters ofthe evoked responses. Examples of the one or more characteristicparameters include amplitude of the evoked responses, width of theevoked responses, and frequency characteristics of the evoked responses.In various embodiments, the one or more characteristic parameters areeach a value measured from one of the evoked responses or being anaverage of values measured from a plurality of the evoked responses. Invarious embodiments, examples of the one or more response signalsinclude a capture verification signal declaring capture of the vagusnerve by the neurostimulation pulses and one or more signalsrepresentative of the one or more characteristic parameters of theevoked responses.

The control circuit 153 includes a parameter adjustor 155, which adjustsone or more parameters of the stimulation parameters using the one ormore response signals. In the illustrated embodiment, the parameteradjustor 155 includes a sensing parameter adjustor 159, a sensingadjustment timer 160, a stimulation parameter adjustor 161, and astimulation adjustment timer 162. The sensing parameter adjustor 159adjusts the one or more detection thresholds used by the comparator 157for detecting the evoked responses. The sensing adjustment timer 160controls the timing of the adjustment of the one or more detectionthresholds according to a specified schedule and/or in response to auser command. The stimulation parameter adjustor 161 adjusts thestimulation intensity by adjusting one or more of the stimulationparameters. Stimulation adjustment timer 162 controls the timing ofadjustment of the stimulation intensity according to a specifiedschedule and/or in response to a user command.

FIG. 22 is a block diagram illustrating an embodiment of an implantablesystem 163. The implantable system 163 includes an IMD 164 and anexternal system 165. The external system 165 is communicatively coupledto the IMD 164 via telemetry link 166. The external system 165 includesa user interface 167. The user interface 167 includes a presentationdevice 168 and a user input device 169. The presentation device 168includes a display screen 170 to display, for example, waveforms of thedetected evoked responses, the one or more response signals, themeasured one or more characteristics parameters, and/or the stimulationintensity. The user input device 169 receives user commands from a usersuch as a physician or other caregiver. Examples of the user commandsinclude a user command for starting a delivery of the neurostimulationpulses, a user command to initiate an adjustment of the one or moredetection thresholds, a user command to initiate an adjustment of thestimulation intensity, and a user command to initiate automatic captureverification as discussed in this document.

In an embodiment, the external system 165 includes a programmerincluding user interface 167. In an embodiment, external system 165includes a patient management system including an external devicecommunicatively coupled to IMD 164 via telemetry link 166 and a remotedevice in a distant location and communicatively coupled to the externaldevice via a communication network. The external device and/or theremote device include the user interface 167.

FIG. 23 is a block diagram illustrating an embodiment of a circuit fordetecting evoked muscular responses. In one embodiment, the circuit isincluded in an IMD. The circuit includes stimulation output circuit 171,a laryngeal activity sensing circuit 172, and an evoked muscularresponse detection circuit 173. The stimulation output circuit 171delivers neurostimulation pulses to the vagus nerve. The laryngealactivity sensing circuit 172 senses a laryngeal signal representative ofactivities of the laryngeal muscle including evoked muscular responseseach evoked by one of the neurostimulation pulses. The evoked muscularresponse detection circuit 173 detects the evoked muscular responsesusing the laryngeal signal. In the illustrated embodiment, evoked neuralresponse detection circuit 173 includes a detection timer 174 and acomparator 175. The detection timer 174 times a detection window duringwhich the detection of an evoked muscular response is anticipated. Thecomparator 175 detects the evoked muscular responses by comparing thesensed laryngeal signal to one or more detection thresholds during thedetection window.

FIG. 24 is a block diagram illustrating an embodiment of a system fordetecting evoked muscular responses. The system includes stimulationelectrodes 148, stimulation output circuit 149, a laryngeal activitysensor 176, a laryngeal activity sensing circuit 177, and an evokedmuscular response detection circuit 178.

The evoked muscular response detection circuit 178 detects the evokedmuscular responses using the sensed laryngeal signal. The evokedmuscular response detection circuit 178 includes comparator 179 and anevoked muscular response measurement module 180, and includes adetection timer 181 if the detection window is used. In one embodiment,the evoked muscular response detection circuit 178 detects the evokedmuscular response according to a specified schedule, such as on aperiodic basis, or in response to a user command. The evoked muscularresponse measurement module 180 measures one or more characteristicparameters. In one embodiment, evoked muscular response measurementmodule 180 measures and trends the one or more characteristicparameters. Examples of the one or more characteristic parametersinclude the amplitude of an evoked muscular response, the sum ofmultiple evoked muscular responses that follow multiple neurostimulationpulses, and the time between the delivery of a neurostimulation pulseand the detection of the evoked muscular response resulting from thedelivery of that neurostimulation pulse. The amplitude of the evokedmuscular responses increases as more motor fibers (A-fibers) arecaptured by delivery of the neurostimulation pulses. More motor fibersare captured as the stimulation intensity increases.

FIG. 25 is a block diagram illustrating an embodiment of a circuit forsensing various laryngeal signals. The circuit includes a laryngealactivity sensor 182 and a laryngeal activity sensing circuit 183. In theillustrated embodiment, laryngeal activity sensor 182 includes EMGsensing electrodes 184, and may further include an accelerometer 185, avoice sensor 186, and a laryngeal activity sensing circuit 183 thatincludes an EMG sensing circuit 187, and may further include an activitysensing circuit 188, and a voice sensing circuit 189. This allows forselection of a laryngeal signal by the user or the system, and alsoallows for use of multiple laryngeal signals for the detection of theevoked muscular responses. The EMG sensing circuit 187 senses the EMGsignal through EMG sensing electrodes 184. The evoked muscular responsedetection circuit detects the evoked muscular responses using the sensedEMG signal.

The accelerometer 185 may be configured to be placed in or on thepatient's body in a location suitable for sensing an acceleration signalas the laryngeal signal. The acceleration signal is indicative ofactivities of the laryngeal muscle including the evoked muscularresponses. In one embodiment, the accelerometer 185 includes animplantable accelerometer. The activity sensing circuit 188 processesthe acceleration signal sensed by the accelerometer 185. The evokedmuscular response detection circuit detects the evoked muscularresponses using the processed acceleration signal.

The voice sensor 186 is configured to be placed in or on the patient'sbody in a location suitable for sensing a voice signal as the laryngealsignal. Vagus nerve stimulation is known to cause change in a patient'svoice, such as hoarseness, by activating the laryngeal muscle. Thus,certain changes in the voice signal are indicative of activities of thelaryngeal muscle including the evoked neuromuscular responses. The voicesensing circuit 189 processes the voice signal sensed by voice sensor186. The evoked muscular response detection circuit detects the evokedmuscular responses using the processed voice signal, such as bydetecting changes in frequency characteristics of the voice signal.

FIG. 26 is a block diagram illustrating an embodiment of a circuit forsensing various laryngeal signals in context. The circuit includes alaryngeal activity sensor 190 and a laryngeal activity sensing circuit191. In the illustrated embodiment, the laryngeal activity sensor 190includes EMG sensing electrodes 192 and the laryngeal activity sensingcircuit 191 includes an EMG sensing circuit 194. The output of thelaryngeal activity sensing circuit 191 is a signal representative of thelaryngeal activity. The circuit further includes context sensor(s) 195such as an accelerometer 196 or a voice sensor 197, and further includescontext sensing circuit 198 such as an activity sensing circuit 199, anda voice sensing circuit 200. The output of the context sensing circuitcan be used to override the processing of the laryngeal activity signal.For example, a vagus nerve capture routine or a titration routine maynot be enabled if the context sensing circuit detects activity ordetects the patient's voice, both of which may adversely interfere withthe EMG sensing of laryngeal activity. In embodiments in which thelaryngeal activity is stored for later processing, the associatedcontext can also be stored with the laryngeal activity. The use of thiscontext information can be used to avoid interference from other muscleactivity that is not attributable to vagus nerve stimulation.

FIG. 27 is a flow chart illustrating an embodiment of a method forautomatic threshold adjustment (also referred to as “Auto-Sense”) forevoked response detection during vagus nerve stimulation. In variousembodiments, the evoked response detection circuit is configured toperform the method according to a specified schedule. In one embodiment,the evoked response detection circuit may be configured to perform themethod periodically or in response to an event, such as monthly, weekly,daily, hourly, once each burst of the neurostimulation pulses, or onceeach pulse of the neurostimulation pulses.

At 201, neurostimulation pulses are delivered to a vagus nerve. At 202,the laryngeal signal is sensed. At 203, the evoked muscular responsesare detected. In one embodiment, an evoked muscular response waveformrepresentative of the evoked muscular responses is detected and stored.The waveform is of one detected evoked muscular response or an averageof several detected evoked muscular responses. In one embodiment, one ormore characteristic parameters of the evoked muscular responses aremeasured. Examples of the one or more characteristic parameters includea maximum amplitude of the sensed laryngeal signal. In one embodiment,the measured one or more characteristic parameters are trended and/orstored for presentation to the user as scheduled or needed. At 204, theone or more detection thresholds are adjusted using the detected evokedmuscular responses. In one embodiment, the detected evoked muscularresponses are compared to a stored baseline response. This includescomparing the evoked response waveform to a stored baseline waveformand/or comparing the one or more characteristic parameters to the storedone or more baseline characteristic parameters. The baseline waveformand/or the one or more baseline characteristic parameters areestablished for a patient during the initial system setup for thepatient (such as implantation of an implantable system), during afollow-up visit, or automatically by an evoked muscular responsedetection circuit when certain criteria are met. At 204, the one or moredetection thresholds are adjusted in response to the detected evokedmuscular responses substantially deviating from the stored baselineresponse. In one embodiment, the user is alerted in response to thedetected evoked muscular responses substantially deviating from thestored baseline response.

FIG. 28 is a flow chart illustrating an embodiment of a method foradjusting stimulation intensity for vagus nerve stimulation. At 205,neurostimulation pulses are delivered to a vagus nerve. At 206, thedelivery of the neurostimulation pulses is controlled using astimulation intensity. The stimulation intensity is adjustable byadjusting stimulation parameters. At 207, the stimulation intensity isswept at specified increments. At 208, an EMG sensor is used to senseactivity of laryngeal muscles. At 209, the sensed activity of thelaryngeal muscles is used to detect activity of the laryngeal muscles.At 210, a stimulation threshold is determined. The stimulation thresholdis a minimum level of the stimulation intensity for providing thedetected activity of the laryngeal muscles. At 211, the stimulationintensity is adjusted for modulating a specified physiologic functionusing the stimulation threshold. In one embodiment, the physiologicfunction includes a cardiovascular function. In an embodiment, thestimulation threshold is trended and used to indicate pathologicalconditions and/or device problems. For example, a substantiallyincreasing stimulation threshold may indicate device problems such aspoor electrical connections or lead failure or pathological conditionssuch as nerve damage. When this happens, the user is alerted forexamining the patient and the neurostimulation system. If thestimulation threshold is not determined after the stimulation intensityis swept through its maximum level, the user is also alerted because anabnormally high stimulation threshold is indicative of the deviceproblems or pathological conditions. The laryngeal signal is detected at208 and the evoked muscular responses are detected at 209. An evokedmuscular response waveform representative of the evoked muscularresponses may be detected and stored. The waveform may be one detectedevoked muscular response or an average of several detected evokedmuscular responses. With reference to 210, the stimulation threshold forone or more specified effects in the evoked muscular response isdetermined. Examples of the one or more specified effects include thatthe amplitude of the sensed laryngeal signal during a detection windowreaches a threshold amplitude, that an evoked muscular response isdetected during the detection window, and a correlation between thedetected evoked muscular response waveform and a stored baselinewaveform reaches a threshold correlation.

FIG. 29 is a flow chart illustrating an embodiment of a method foradjusting stimulation intensity for vagus nerve stimulation duringimplantation of an implantable medical device. At 212, a lead isimplanted with stimulation electrodes on or near a vagus nerve forstimulating the vagus nerve of a patient and with EMG sensor(s) forsensing laryngeal activity. The stimulation electrodes are connected toa neurostimulator including a stimulation output circuit and a controlcircuit for delivering neurostimulation pulses to the vagus nerve. Theneurostimulator may be an external device for use during the implantableprocedure or the implantable medical device intended to be implantedinto the patient. At 213, the neurostimulation pulses are deliveredthrough the stimulation electrodes. The delivery of the neurostimulationpulses is controlled using a stimulation intensity that starts at aspecified low level. The stimulation intensity is controlled by one ormore stimulation parameters. At 214, the physiological signal is sensed.At 215, the evoked responses, including waveforms and measuredinformation, are presented to the user on a display screen. Examples ofthe presented information include the amplitude of the evoked muscularresponses, the sum of a plurality of the evoked muscular responses, thetime between the delivery of a neurostimulation pulse and the detectionof the evoked muscular response resulting from the delivery of thatneurostimulation pulse, and the stimulation parameters including thosecontrolling the stimulation intensity. At 217, if the user is notsatisfied with the evoked neural responses at 216, the stimulationintensity is increased by increasing the pulse amplitude and/or thepulse width. If the stimulation intensity cannot be further increased,the user is alerted for examining the patient for possible pathologicalconditions preventing effectiveness of the neurostimulation and/or thesystem for possible device and/or connection problems. At 218, if theuser is satisfied with the evoked neural responses associated with alevel of the stimulation intensity at 216, that level of the stimulationintensity is stored and used to determine the subsequent vagus nervestimulation therapy delivered from the implantable medical device.

FIG. 30 is a flow chart illustrating an embodiment of a method foradjusting stimulation intensity for vagus nerve stimulation duringfollow-up visits by the patient using the implantable medical device. At219, an intensity adjustment feature of the implantable medical deviceis initiated by the user. In one embodiment, a stimulation adjustmenttimer initiates the adjustment of stimulation intensity in response to auser command entered by the user using an external systemcommunicatively coupled to the implantable medical device. At 220,stimulation intensity levels are swept. This includes incrementallyincreasing the pulse amplitude and/or the pulse width from specified lowvalues. At 221, the laryngeal signal is sensed using the EMG sensor thatwas implanted in the patient with the stimulation electrodes. At 222,the evoked laryngeal muscular responses are detected. At 223, datarepresentative of the detected evoked responses are telemetered to theexternal system. At 224, the evoked responses, including waveforms andmeasured information, are presented to the user on a display screen ofthe external system using the telemetered data. When the physiologicalsignal includes the laryngeal signal, examples of the presentedinformation include the amplitude of the evoked muscular responses, thesum of a plurality of the evoked muscular responses, the time betweenthe delivery of a neurostimulation pulse and the detection of the evokedmuscular response resulting from the delivery of that neurostimulationpulse, and stimulation parameters including those controlling thestimulation intensity. At 226, if the user is not satisfied with theevoked neural responses at 225, the stimulation intensity is increasedby increasing the pulse amplitude and/or the pulse width. If thestimulation intensity cannot be further increased, the user is alertedfor examining the patient for possible pathological conditionspreventing effectiveness of the neurostimulation and/or the system forpossible device and/or connection problems. At 227, if the user issatisfied with the evoked neural responses associated with a level ofthe stimulation intensity at 225, that level of the stimulationintensity (in terms of the pulse amplitude and the pulse width) isstored and used to determine the subsequent vagus nerve stimulationtherapy delivered from the implantable medical device.

FIG. 31 is a flow chart illustrating an embodiment of a method forautomatic capture verification (also referred to as “Auto-Capture”) forvagus nerve stimulation. The automatic capture verification providesautomatic verification of capture of the vagus nerve by neurostimulationpulses and adjustment of the stimulation intensity. The control circuitmay be configured to perform the automatic capture verificationaccording to a schedule or periodically or according to an event, suchas monthly, weekly, daily, hourly, once each burst of theneurostimulation pulses, or once each pulse of the neurostimulationpulses. At 228, neurostimulation pulses are delivered to a vagus nerve.At 229, the delivery of the neurostimulation pulses is controlled usinga stimulation intensity. The stimulation intensity is adjusted byadjusting stimulation parameters. At 230, a capture verification isperformed. At 231, the laryngeal signal is sensed. At 232, one of theevoked muscular responses for each pulse of the neurostimulation pulsesdelivered is detected. At 233, the stimulation intensity is adjusted inresponse to a specified one or more of the evoked muscular responses notdetected (i.e. non-capture) for a specified number of theneurostimulation pulses delivered. In one embodiment, the stimulationintensity is adjusted in response to an evoked muscular response notbeing detected for one of the neurostimulation pulses delivered. Inanother embodiment, the stimulation intensity is adjusted in response tothe evoked muscular response not being detected for a specified firstnumber of the neurostimulation pulses delivered out of a specifiedsecond number of the neurostimulation pulses delivered. In anotherembodiment, the stimulation intensity is adjusted in response to anevoked muscular response not being detected for a rolling average numberof the neurostimulation pulses delivered. The stimulation intensity maybe lowered to prevent unnecessary energy delivered with theneurostimulation pulses to promote device longevity. If an unacceptabledegree of loss of capture occurs when the stimulation intensity is setto about the available maximum level, the user is alerted for examiningthe patient for possible pathological conditions preventingeffectiveness of neurostimulation and/or the system for possible deviceand/or connection problems.

In one embodiment, each of the automatic threshold adjustment(Auto-Sense), automatic stimulation intensity adjustment(Auto-Threshold), and automatic capture verification (Auto-Capture) isdisabled or delayed if noise in the sensed physiological signal exceedsa specified threshold noise level, due to the patient's activities andspeeches for example. In one embodiment, each of the automatic thresholdadjustment (Auto-Sense), automatic stimulation intensity adjustment(Auto-Threshold), and automatic capture verification (Auto-Capture) isperformed with various parameters such as the detection thresholdsadjusted for the patient's posture, activity level and voice.

As will be understood by one of ordinary skill in the art upon readingand comprehending the present subject matter, various embodiments of thepresent subject matter improve the ability to quickly and accuratelyimplant and program a neural stimulation system and intermittentlyreprogram the system, improve patient acceptance of therapy and maintainefficacious levels of therapy. The modules and other circuitry shown anddescribed herein can be implemented using software, hardware, firmwareand combinations thereof.

The above detailed description is intended to be illustrative, and notrestrictive. Other embodiments will be apparent to those of skill in theart upon reading and understanding the above description. The scope ofthe invention should, therefore, be determined with reference to theappended claims, along with the full scope of equivalents to which suchclaims are entitled.

1. (canceled)
 2. A method for detecting vagus nerve capture using animplanted lead, comprising: delivering neurostimulation pulses throughthe lead to a vagus nerve; sensing EMG signals from laryngeal muscleactivity using the lead; and detecting evoked laryngeal muscle activityevoked by the neurostimulation pulses using the sensed EMG signals. 3.The method of claim 2, wherein the lead includes a vagal nerve cuff, andwherein sensing EMG signals includes sensing EMG signals from laryngealmuscle activity using electrodes on the vagal nerve cuff.
 4. The methodof claim 3, wherein delivering neurostimulation pulses includesdelivering neurostimulation pulses to the vagus nerve using theelectrodes on the vagal nerve cuff.
 5. The method of claim 2, whereinthe lead is configured to be intravascularly inserted into an internaljugular vein, and wherein delivering neurostimulation pulses includestransvascularly stimulating the vagus nerve using the lead in theinternal jugular vein, and sensing EMG signals from laryngeal activityincludes using the lead in the internal jugular vein to sense EMGsignals.
 6. The method of claim 2, wherein the lead has a first set ofelectrodes and a second set of electrodes, and the first set ofelectrodes is proximate to a distal end of the lead, wherein sensing EMGsignals from laryngeal activity includes using the first set ofelectrodes to sense EMG signals from laryngeal muscle activity, anddelivering neurostimulation pulses includes using the second set ofelectrodes to deliver neurostimulation pulses to the vagus nerve throughthe lead.
 7. The method of claim 2, wherein the lead is configured to beimplanted extravascularly within a carotid sheath, wherein deliveringneural stimulation includes using the lead implanted extravascularlywithin the carotid sheath to stimulate the vagus nerve, and sensing EMGsignals from laryngeal activity includes using the lead implantedextravascularly within the carotid sheath to sense EMG signals fromlaryngeal activity.
 8. The method of claim 2, wherein: the lead has afirst set of electrodes and a second set of electrodes, wherein thefirst set of electrodes is proximate to a distal end of the lead and,when implanted, the second set of electrodes is more caudal than thefirst set of electrodes and is more cranial than a point where therecurrent laryngeal nerve branches from the vagus nerve; sensing EMGsignals from laryngeal activity includes using the first set ofelectrodes to sense EMG signals from laryngeal muscle activity; anddelivering neural stimulation pulses includes using the second set ofelectrodes to deliver neurostimulation pulses to the vagus nerve throughthe lead.
 9. The system of claim 2, further comprising: timing a delayinterval after delivery of one of the neurostimulation pulses, andtiming a detection window starting upon expiration of the delayinterval; and detecting the evoked laryngeal muscle activity bycomparing the sensed EMG signals within the detection window to atemplate or by comparing a value derived from the sensed EMG signalswithin the detection window to a threshold value.
 10. The method ofclaim 9, wherein the detection window begins about 8 ms and ends about12 ms after delivery of one of the stimulation pulses.
 11. The method ofclaim 9, wherein detecting the evoked laryngeal muscle activity includescomparing the sensed EMG signals to a patient-specific template.
 12. Themethod of claim 9, further comprising generating an active rechargepulse after each neurostimulation pulse, and completing the activerecharge pulse during the time delay interval.
 13. The method of claim9, further comprising generating a passive recharge after eachneurostimulation pulse, interrupting the passive recharge during thedetection window, and resuming the passive recharge after completion ofthe detection window.
 14. The method of claim 2, further comprisingmeasuring one or more characteristic parameters of the evoked laryngealmuscle activity and generating a signal representative of the one ormore characteristic parameters.
 15. The method of claim 2, enablingdetection of the evoked laryngeal muscle activity according to aprogrammed schedule.
 16. The method of claim 2, further comprisingenabling detection of the evoked laryngeal muscle activity in responseto a physician-initiated command signal.
 17. The method of claim 2,further comprising enabling detection of the evoked laryngeal muscleactivity in response to a patient-initiated command signal.
 18. Themethod of claim 2, further comprising detecting an event, andautomatically enabling detection of the evoked laryngeal muscle activityin response to detecting the event.
 19. The method of claim 2, furthercomprising sensing context to provide a contextual signal, and using thecontextual signal and the sensed EMG signals to detect evoked laryngealmuscle activity evoked by the neurostimulation pulses.
 20. The method ofclaim 2, further comprising automatically adjusting a parameter of theneurostimulation pulses, using a control circuit, to evoke desiredlaryngeal muscle activity.
 21. The method of claim 2, wherein the methodis performed by an implanted medical device.